Medical device and methods

ABSTRACT

Hysteroscopic system includes a hysteroscope having a main body coupled to an extension portion. The extension portion may be a shaft configured to extend transcervically to a patient&#39;s uterine cavity. First, second, and third channels extend from the main body to a distal end of the extension portion. A fluid source is coupleable to a proximal end of the first channel, and a pressure sensor is coupleable to a proximal end of the second channel. A tissue resecting probe is configured for introduction through the third channel. At least one resistance feature is included which is configured to provide a selected level of resistance to axial sliding of the probe through the third channel while permitting rotation of the probe within the third channel.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.13/745,439, filed Jan. 18, 2013, now U.S. Pat. No. 9,439,677, whichclaims the benefit of U.S. Provisional Application No. 61/589,168, filedJan. 20, 2012; U.S. Provisional Application No. 61/635,803, filed Apr.19, 2012; and U.S. Provisional Application No. 61/659,312, filed Jun.13, 2012; the full disclosures of which are incorporated herein byreference.

TECHNICAL FIELD

The present invention relates to systems and methods for the resectionand extraction of uterine fibroid tissue, polyps and other abnormaluterine tissue.

BACKGROUND

Uterine fibroids are non-cancerous tumors that develop in the wall ofuterus. Such fibroids occur in a large percentage of the femalepopulation, with some studies indicating that up to 40 percent of allwomen have fibroids. Uterine fibroids can grow over time to be severalcentimeters in diameter and symptoms can include menorrhagia,reproductive dysfunction, pelvic pressure and pain.

One current treatment of fibroids is hysteroscopic resection ormyomectomy which involves transcervical access to the uterus with ahysteroscope together with insertion of a cutting instrument through aworking channel in the hysteroscope. The cutting instrument may be amechanical tissue cutter or an electrosurgical resection device such asa cutting loop. Mechanical cutting devices are disclosed in U.S. Pat.Nos. 7,226,459; 6,032,673 and 5,730,752 and U.S. Published Patent Appl.No. 2009/0270898. An electrosurgical resecting device is disclosed inU.S. Pat. No. 5,906,615.

While hysteroscopic resection can be effective in removing uterinefibroids and polyps, one difficulty that may be encountered withresecting instruments is control of the instrument in the workingchannel of the hysteroscope. Typically, the resecting instrument is freeto both rotate and axially translate within the working channel. Whilerotation of the instrument during use may be needed, it would bepreferable to have the resecting instrument remain axially stationaryrelative to the hysteroscope during use, particularly with windowedtubular resection instruments. What is needed therefore is a system thatcan allow the resecting instrument to rotate freely while inhibitingaxial displacement relative to the hysteroscope to provide for effectiveresection and removal of fibroid and polyp tissue through thehysteroscope.

SUMMARY

The present invention provides methods for resecting and removing targettissue from a patient's body, such as fibroids, polyps and abnormaltissue from a uterus. The tissue is resected and captured in a probe,catheter, or other tissue-removal device, and expelled from the capturedevice by vaporizing a fluid, typically a liquid, adjacent to thecaptured tissue in order to propel the tissue from the device, typicallythrough an extraction or other lumen present in a body or shaft of thedevice. Exemplary embodiments, the tissue removal device comprise areciprocating blade or the like, where the blade may be advanced past awindow on the device in order to resect a tissue strip and capture thestrip within an interior volume or receptacle on the device. The liquidor other expandable fluid is also present in the device, and energy isapplied to the fluid in order to cause rapid expansion, e.g.,vaporization, in order to propel the severed tissue strip through theextraction lumen. In this way, the dimensions of the extraction lumencan be reduced, particularly in the distal regions of the device wheresize is of critical importance.

In a first aspect of the present invention, an improved hysteroscopicsystem comprises a hysteroscope having a main body coupled to anextension portion. The extension portion, typically a shaft, isconfigured to extend transcervically to a patient's uterine cavity.First, second, and third channels extend from the main body to a distalend of the extension portion, typically being formed inside of a tubularwall or structure of the extension portion. A fluid source is coupleableto a proximal end of the first channel, and a pressure sensor iscoupleable to a proximal end of the second channel. A tissue resectingprobe is configured for introduction through the third channel. At leastone resistance feature is included which is configured to provide aselected level of resistance to axial sliding of the probe through thethird channel while permitting rotation of the probe within the thirdchannel.

The resistance feature may comprise a non-linear third channel, i.e., athird channel having a non-linear centerline. Typically, the non-linearcenterline will be a curved centerline, and the curved centerlineextends over a length in the range from 4 cm to 8 cm. The curvedcenterline will usually have a radius in the range from 150 mm to 900mm. In other aspects, the curved centerline has a proximal end which isoffset by a distance in the range from 2 mm to 5 mm from a hypotheticalcenterline of the third channel if it were straight.

Alternatively, the resistance feature may comprise detents formed in awall of the shaft of the probe and detent-engaging elements within acomponent of the endoscope.

In other embodiments, the pressure sensor may be disposable. The secondchannel may have a cross-sectional area of greater than 0.5 mm², oftengreater than 1.0 mm².

The system of the present invention may further comprise a controllercoupled to the fluid source and adapted to selectively control flows tothe uterine cavity through the first channel at a rate between 0 ml/minand 750 ml/min. The controller may be coupled to the pressure sensor andmay be adapted to selectively control pressure in the uterine cavity atany level between 0 mmHg and 150 mmHg. The controller may be furtheradapted to selectively control flows from the uterine cavity through theprobe in the third channel at any rate between 0 ml/min and 750 ml/min.

In a second aspect of the present invention, a system for accessing auterine cavity comprises an elongated body extending longitudinallyabout a first axis from a handle end through a shaft portion to a distalend. First, second and third channels extend from the handle end to adistal region of the shaft portion. A positive pressure fluid source isin communication with the first channel, and a pressure sensor isdetachably coupled to a proximal end of the second channel. The thirdchannel has a curved centerline and is configured for fluid outflowstherethrough.

The system may further comprise a pressure relief valve in the handleend, and the third channel may be configured to receive an elongatedtool.

In a third aspect of the present invention, a method for resectingfibroids or polyps in a uterus comprises transcervically introducing adistal end of an extension portion of a hysteroscope into the uterus. Aresecting instrument is advanced through a curved channel of thehysteroscope so that a resecting end of the instrument extends form adistal end of the extension portion. The resecting end of the instrumentis engaged against a fibroid or polyp while the instrument remainswithin the curved channel. The curve advantageously provides resistanceto axial displacement of the resecting instrument shaft relative to thechannel while the resecting end is engaged. The resistance, however, issuch that the curve channel does not substantially inhibit rotationwhich is desirable.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a plan view of an assembly including a hysteroscope and atissue resecting device corresponding to the invention that is insertedthrough a working channel of the hysteroscope.

FIG. 2 is a schematic perspective view of a fluid management system usedfor distending the uterus and for assisting in electrosurgical tissueresection and extraction.

FIG. 3 is a cross-sectional view of the shaft of the hysteroscope ofFIG. 1 showing various channels therein.

FIG. 4 is a schematic side view of the working end of theelectrosurgical tissue resecting device of FIG. 1 showing an outersleeve and a reciprocating inner sleeve and an electrode arrangement.

FIG. 5 is a schematic perspective view of the working end of the innersleeve of FIG. 4 showing its electrode edge.

FIG. 6A is a schematic cut-away view of a portion of outer sleeve, innerRF resection sleeve and a tissue-receiving window of the outer sleeve.

FIG. 6B is a schematic view of a distal end portion another embodimentof inner RF resection sleeve.

FIG. 7A is a cross sectional view of the inner RF resection sleeve ofFIG. 6B taken along line 7A-7A of FIG. 6B.

FIG. 7B is another cross sectional view of the inner RF resection sleeveof FIG. 6B taken along line 7B-7B of FIG. 6B.

FIG. 8 is a schematic view of a distal end portion of another embodimentof inner RF resection sleeve.

FIG. 9A is a cross sectional view of the RF resection sleeve of FIG. 8taken along line 9A-9A of FIG. 8.

FIG. 9B is a cross sectional view of the RF resection sleeve of FIG. 8taken along line 9B-9B of FIG. 8.

FIG. 10A is a perspective view of the working end of the tissueresecting device of FIG. 1 with the reciprocating RF resection sleeve ina non-extended position.

FIG. 10B is a perspective view of the tissue resecting device of FIG. 1with the reciprocating RF resection sleeve in a partially extendedposition.

FIG. 10C is a perspective view of the tissue resecting device of FIG. 1with the reciprocating RF resection sleeve in a fully extended positionacross the tissue-receiving window.

FIG. 11A is a sectional view of the working end of the tissue resectingdevice of FIG. 10A with the reciprocating RF resection sleeve in anon-extended position.

FIG. 11B is a sectional view of the working end of FIG. 10B with thereciprocating RF resection sleeve in a partially extended position.

FIG. 11C is a sectional view of the working end of FIG. 10C with thereciprocating RF resection sleeve in a fully extended position.

FIG. 12A is an enlarged sectional view of the working end of tissueresecting device of FIG. 11B with the reciprocating RF resection sleevein a partially extended position showing the RF field in a first RF modeand plasma resection of tissue.

FIG. 12B is an enlarged sectional view of the working end of FIG. 11Cwith the reciprocating RF resection sleeve almost fully extended andshowing the RF fields switching to a second RF mode from a first RF modeshown in FIG. 12.

FIG. 12C is an enlarged sectional view of the working end of FIG. 11Cwith the reciprocating RF resection sleeve again almost fully extendedand showing the explosive vaporization of a captured liquid volume toexpel resected tissue in the proximal direction.

FIG. 13 is an enlarged perspective view of a portion of the working endof FIG. 12C showing an interior chamber and a fluted projecting element.

FIG. 14 is a sectional view of the working end of FIG. 12C showing aninterior chamber and a variation of a projecting element.

FIG. 15 is a plan view of another fibroid removal system including anendoscope and an electrosurgical tissue resecting device that isinserted through a curved working channel of the hysteroscope.

FIG. 16 is a cut-away view of the hysteroscope of FIG. 15 showing adisposable adapter component carrying a seal assembly and furthershowing a working channel with a curved portion in the main body of theendoscope.

FIG. 17 is a sectional view of a handle portion of an endoscope havingan expanded cross-section channel that provides a fluid reservoir and asolenoid-relief valve mechanism for rapid release of fluid from thesystem to reduce uterine cavity pressure.

FIG. 18 is a cross-section of the handle portion of FIG. 17 taken alongline 18-18 of FIG. 17.

FIG. 19 is a sectional view of a handle portion of another endoscopesimilar to that of FIG. 17.

FIG. 20A is a schematic view of an annular flow channel and fluidreservoir in the endoscope handle portion of FIGS. 17-19.

FIG. 20B is a schematic view of an annular flow channel in an endoscopehandle portion without the fluid reservoir as in the variation of FIGS.17-19.

FIG. 21 is a sectional view of a handle portion of another endoscopesimilar to that of FIGS. 17-18 with an optical sensor.

FIG. 22 is a sectional view of a handle portion of another endoscopesimilar to that of FIGS. 17-18 with a passive pressure relief valve.

DETAILED DESCRIPTION

FIG. 1 illustrates an assembly that comprises an endoscope 50 used forhysteroscopy together with an electrosurgical tissue resecting device100 extending through a working channel 102 of the endoscope. Theendoscope or hysteroscope 50 has a handle 104 coupled to an elongatedshaft 105 having a diameter of 5 mm to 7 mm. The working channel 102therein may be round, D-shaped or any other suitable shape. Theendoscope shaft 105 is further configured with an optics channel 106 andone or more fluid inflow/outflow channels 108 a, 108 b (FIG. 3) thatcommunicate with valve-connectors 110 a, 110 b configured for couplingto a fluid inflow source 120 thereto, or optionally a negative pressuresource 125 (FIGS. 1-2). The fluid inflow source 120 is a component of afluid management system 126 as is known in the art (FIG. 2) whichcomprises a fluid container 128 and pump mechanism 130 which pumps fluidthrough the hysteroscope 50 into the uterine cavity. As can be seen inFIG. 2, the fluid management system 126 further includes the negativepressure source 125 (which can comprise an operating room wall suctionsource) coupled to the tissue resecting device 100. The handle 104 ofthe endoscope includes the angled extension portion 132 with optics towhich a videoscopic camera 135 can be operatively coupled. A lightsource 136 also is coupled to light coupling 138 on the handle of thehysteroscope 50. The working channel 102 of the hysteroscope isconfigured for insertion and manipulation of the tissue resecting andextracting device 100, for example to treat and remove fibroid tissue.In one embodiment, the hysteroscope shaft 105 has an axial length of 21cm, and can comprise a 0° scope, or 15° to 30° scope.

Still referring to FIG. 1, the tissue resecting device 100 has a highlyelongated shaft assembly 140 configured to extend through the workingchannel 102 in the hysteroscope. A handle 142 of the tissue resectingdevice 100 is adapted for manipulating the electrosurgical working end145 of the device. In use, the handle 142 can be manipulated bothrotationally and axially, for example, to orient the working end 145 toresect targeted fibroid or polyp tissue. The tissue resecting device 100has subsystems coupled to its handle 142 to enable electrosurgicalresection of targeted tissue. A radiofrequency generator or RF source150 and controller 155 are coupled to at least one RF electrode carriedby the working end 145 as will be described in detail below. In oneembodiment shown in FIG. 1, an electrical cable 156 and negativepressure source 125 are operatively coupled to a connectors 158 and 159in handle 142. The electrical cable couples the RF source 150 to theelectrosurgical working end 145. The negative pressure source 125communicates with a tissue-extraction channel 160 in the shaft assembly140 of the tissue extraction device 100 (FIG. 4).

FIG. 1 further illustrates a seal housing 162 that carries a flexibleseal 164 carried by the hysteroscope handle 104 for sealing the shaft140 of the tissue resecting device 100 in the working channel 102 toprevent distending fluid from escaping from a uterine cavity.

In one embodiment as shown in FIG. 1, the handle 142 of tissue resectingdevice 100 includes a motor drive 165 for reciprocating or otherwisemoving a resecting component of the electrosurgical working end 145 aswill be described below. The handle 142 optionally includes one or moreactuator buttons 166 for actuating the device. In another embodiment, afootswitch can be used to operate the device. In one embodiment, thesystem includes a switch or control mechanism to provide a plurality ofreciprocation speeds, for example 1 Hz, 2 Hz, 3 Hz, 4 Hz and up to 8 Hz.Further, the system can include a mechanism for moving and locking thereciprocating sleeve in a non-extended position and in an extendedposition. Further, the system can include a mechanism for actuating asingle reciprocating stroke.

Referring to FIGS. 1 and 4, an electrosurgical tissue resecting devicehas an elongate shaft assembly 140 extending about longitudinal axis 168comprising an exterior or first outer sleeve 170 with passageway orlumen 172 therein that accommodates a second or inner sleeve 175 thatcan reciprocate (and optionally rotate or oscillate) in lumen 172 toresect tissue as is known in that art of such tubular resection devices.In one embodiment, the tissue-receiving window 176 in the outer sleeve170 has an axial length ranging between 10 mm and 30 mm and extends in aradial angle about outer sleeve 170 from about 45° to 210° relative toaxis 168 of the sleeve. The outer and inner sleeves 170 and 175 cancomprise a thin-wall stainless steel material and can function asopposing polarity electrodes as will be described in detail below. FIGS.6A-8 illustrate insulating layers carried by the outer and inner sleeves170 and 175 to limit, control and/or prevent unwanted electrical currentflows between certain portions of the sleeve. In one embodiment, astainless steel outer sleeve 170 has an O.D. of 0.143″ with an I.D. of0.133″ and with an inner insulating layer (described below) the sleevehas a nominal I.D. of 0.125″. In this embodiment, the stainless steelinner sleeve 175 has an O.D. of 0.120″ with an I.D. of 0.112″. The innersleeve 175 with an outer insulating layer has a nominal O.D. of about0.123″ to 0.124″ to reciprocate in lumen 172. In other embodiments,outer and or inner sleeves can be fabricated of metal, plastic, ceramicor a combination thereof. The cross-section of the sleeves can be round,oval or any other suitable shape.

As can be seen in FIG. 4, the distal end 177 of inner sleeve 175comprises a first polarity electrode with distal resecting electrodeedge 180 about which plasma can be generated. The electrode edge 180also can be described as an active electrode during tissue resectionsince the electrode edge 180 then has a substantially smaller surfacearea than the opposing polarity or return electrode. In one embodimentin FIG. 4, the exposed surfaces of outer sleeve 170 comprises the secondpolarity electrode 185, which thus can be described as the returnelectrode since during use such an electrode surface has a substantiallylarger surface area compared to the functionally exposed surface area ofthe active electrode edge 180.

In one aspect of the invention, the inner sleeve or resecting sleeve 175has an interior tissue extraction lumen 160 with first and secondinterior diameters that are adapted to electrosurgically resect tissuevolumes rapidly—and thereafter consistently extract the resected tissuestrips through the highly elongated lumen 160 without clogging. Nowreferring to FIGS. 5 and 6A, it can be seen that the inner sleeve 175has a first diameter portion 190A that extends from the handle 142(FIG. 1) to a distal region 192 of the sleeve 175 wherein the tissueextraction lumen transitions to a smaller second diameter lumen 190Bwith a reduced diameter indicated at B which is defined by the electrodesleeve element 195 that provides the electrode edge 180. The axiallength C of the reduced cross-section lumen 190B can range from about 2mm to 20 mm. In one embodiment, the first diameter A is 0.112″ and thesecond reduced diameter B is 0.100″. As shown in FIG. 5, the innersleeve 175 can be an electrically conductive stainless steel and thereduced diameter electrode portion also can comprise a stainless steelelectrode sleeve element 195 that is welded in place by weld 196 (FIG.6A). In another alternative embodiment, the electrode and reduceddiameter electrode sleeve element 195 comprises a tungsten tube that canbe press fit into the distal end 198 of inner sleeve 175. FIGS. 5 and 6Afurther illustrates the interfacing insulation layers 202 and 204carried by the first and second sleeves 170, 175, respectively. In FIG.6A, the outer sleeve 170 is lined with a thin-wall insulating material200, such as PFA, or another material described below. Similarly, theinner sleeve 175 has an exterior insulating layer 202. These coatingmaterials can be lubricious as well as electrically insulating to reducefriction during reciprocation of the inner sleeve 175.

The insulating layers 200 and 202 described above can comprise alubricious, hydrophobic or hydrophilic polymeric material. For example,the material can comprise a bio-compatible material such as PFA,TEFLON®, polytetrafluroethylene (PTFE), FEP (fluorinatedethylenepropylene), polyethylene, polyamide, ECTFE(ethylenechlorotrifluoro-ethylene), ETFE, PVDF, polyvinyl chloride orsilicone.

Now turning to FIG. 6B, another variation of inner sleeve 175 isillustrated in a schematic view together with a tissue volume beingresected with the plasma electrode edge 180. In this embodiment, as inother embodiments in this disclosure, the RF source operates at selectedoperational parameters to create a plasma around the electrode edge 180of electrode sleeve 195 as is known in the art. Thus, the plasmagenerated at electrode edge 180 can resect and ablate a path P in thetissue 220, and is suited for resecting fibroid tissue and otherabnormal uterine tissue. In FIG. 6B, the distal portion of the innersleeve 175 includes a ceramic collar 222 which is adjacent the distaledge 180 of the electrode sleeve 195. The ceramic 222 collar functionsto confine plasma formation about the distal electrode edge 180 andfunctions further to prevent plasma from contacting and damaging thepolymer insulating layer 202 on the inner sleeve 175 during operation.In one aspect of the invention, the path P in tissue 220 made with theplasma at electrode edge 180 provides a path P having an ablated widthindicated at W, wherein such path width W is substantially wide due totissue vaporization. This removal and vaporization of tissue in path Pis substantially different than the effect of cutting similar tissuewith a sharp blade edge, as in various prior art devices. A sharp bladeedge can divide tissue (without cauterization) but applies mechanicalforce to the tissue and may prevent a large cross section slug of tissuefrom being cut. In contrast, the plasma at the electrode edge 180 canvaporize a path P in tissue without applying any substantial force onthe tissue to thus resect larger cross sections or slugs strips oftissue. Further, the plasma ablation effect reduces the cross section oftissue strip 225 received in the tissue-extraction lumen 190B. FIG. 6Bdepicts a tissue strip to 225 entering lumen 190B which has such asmaller cross-section than the lumen due to the vaporization of tissue.Further, the cross section of tissue 225 as it enters the largercross-section lumen 190A results in even greater free space 196 aroundthe tissue strip 225. Thus, the resection of tissue with the plasmaelectrode edge 180, together with the lumen transition from the smallercross-section (190B) to the larger cross-section (190A) of thetissue-extraction lumen 160 can significantly reduce or eliminate thepotential for successive resected tissue strips 225 to clog the lumen.Prior art mechanical cutting devices with such small diametertissue-extraction lumens typically have problems with tissue clogging.

In another aspect of the invention, the negative pressure source 225coupled to the proximal end of tissue-extraction lumen 160 (see FIGS. 1and 4) also can assist in aspirating and moving tissue strips 225 in theextraction lumen 160 in the proximal direction to a collection reservoir(not shown) outside the handle 142 of the device.

FIGS. 7A-7B illustrate the change in lumen diameter of resection sleeve175 of FIG. 6B. FIG. 8 illustrates the distal end of a variation ofresection sleeve 175′ which is configured with an electrode resectionelement 195′ that is partially tubular in contrast to the previouslydescribed tubular electrode element 195 (FIGS. 5 and 6A). FIGS. 9A-9Bagain illustrate the change in cross-section of the tissue-extractionlumen between reduced cross-section region 190B′ and the increasedcross-section region 190A′ of the resection sleeve 175′ of FIG. 8. Thus,the functionality remains the same whether the resection electrodeelement 195′ is tubular or partly tubular. In FIG. 8A, the ceramiccollar 222′ is shown, in one variation, as extending only partiallyaround sleeve 175 to cooperate with the radial angle of resectionelectrode element 195′. Further, the variation of FIG. 8 illustratesthat the ceramic collar 222′ has a larger outside diameter thaninsulating layer 202. Thus, friction may be reduced since the shortaxial length of the ceramic collar 222′ interfaces and slides againstthe interfacing insulating layer 200 about the inner surface of lumen172 of outer sleeve 170.

In general, one aspect of the invention comprises a tissue resecting andextracting device (FIGS. 10A-11C) that includes first and secondconcentric sleeves having an axis and wherein the second (inner) sleeve175 has an axially-extending tissue-extraction lumen therein, andwherein the second sleeve 175 is moveable between axially non-extendedand extended positions relative to a tissue-receiving window 176 infirst sleeve 170 to resect tissue, and wherein the tissue extractionlumen 160 has first and second cross-sections. The second sleeve 175 hasa distal end configured as a plasma electrode edge 180 to resect tissuedisposed in tissue-receiving window 176 of the first sleeve 170.Further, the distal end of the second sleeve, and more particularly, theelectrode edge 180 is configured for plasma ablation of a substantiallywide path in the tissue. In general, the tissue-extraction device isconfigured with a tissue extraction lumen 160 having a distal endportion with a reduced cross-section that is smaller than across-section of medial and proximal portions of the lumen 160.

In one aspect of the invention, referring to FIGS. 7A-7B and 9A-9B, thetissue-extraction lumen 160 has a reduced cross-sectional area in lumenregion 190A proximate the plasma tip or electrode edge 180 wherein saidreduced cross section is less that 95%, 90%, 85% or 80% than the crosssectional area of medial and proximal portions 190B of thetissue-extraction lumen, and wherein the axial length of thetissue-extraction lumen is at least 10 cm, 20 cm, 30 cm or 40 cm. In oneembodiment of tissue resecting device 100 for hysteroscopic fibroidresection and extraction (FIG. 1), the shaft assembly 140 of the tissueresecting device is 35 cm in length.

FIGS. 10A-10C illustrate the working end 145 of the tissue resectingdevice 100 with the reciprocating resecting sleeve or inner sleeve 175in three different axial positions relative to the tissue receivingwindow 176 in outer sleeve 170. In FIG. 10A, the resecting sleeve 175 isshown in a retracted or non-extended position in which the sleeve 175 isat it proximal limit of motion and is prepared to advance distally to anextended position to thereby electrosurgically resect tissue positionedin and/or suctioned into in window 176. FIG. 10B shows the inner sleeve175 moved and advanced distally to a partially advanced or medialposition relative to tissue receiving window 176. FIG. 10C illustratesthe inner sleeve 175 fully advanced and extended to the distal limit ofits motion wherein the plasma ablation electrode 180 has extended pastthe distal end 226 of tissue-receiving window 176 at which moment theresected tissue strip 225 is excised from tissue volume 220 and capturedin reduced cross-sectional lumen region 190A.

Now referring to FIGS. 10A-10C, FIGS. 11A-11C and FIGS. 12A-12C, anotheraspect of the invention comprises “tissue displacement” mechanismsprovided by multiple elements and processes to “displace” and movetissue strips 225 (FIG. 12A) in the proximal direction in lumen 160 ofinner sleeve 175 to thus ensure that tissue does not clog the lumen ofthe inner sleeve 175. As can be seen in FIG. 10A and the enlarged viewsof FIGS. 11A-11C, one tissue displacement mechanism comprises aprojecting element 230 that extends proximally from distal tip 232 whichis fixedly attached to outer sleeve 170. The projecting element 230extends proximally along central axis 168 in a distal chamber 240defined by outer sleeve 170 and distal tip 232. In one embodimentdepicted in FIG. 11A, the shaft-like projecting element 230, in a firstfunctional aspect, comprises a mechanical pusher that functions to pusha captured tissue strip 225 proximally from the small cross-sectionlumen 190B of inner sleeve 175 (FIG. 12A) as the inner sleeve 175 movesto its fully advanced or extended position.

In a second functional aspect, the chamber 240 in the distal end ofsleeve 170 is configured to capture a volume of saline distending fluid244 (FIG. 12A) from the working space, and wherein the existing RFelectrodes of the working end 145 are further configured to explosivelyvaporize the captured fluid 244 to generate proximally-directed forceson tissue strips 225 resected and disposed in lumen 160 of the innersleeve 175 (FIGS. 12B and 12C). Both of these functional elements andprocesses (tissue displacement mechanisms) can apply a substantialmechanical force on the captured tissue strips 225 by means of theexplosive vaporization of liquid in chamber 240 and can function to movetissue strips 225 in the proximal direction in the tissue-extractionlumen 160. It has been found that using the combination of multiplefunctional elements and processes can virtually eliminate the potentialfor tissue clogging the tissue extraction lumen 160.

More particularly, FIGS. 12A-12C illustrate the functional aspects ofthe tissue displacement mechanisms and the subsequent explosivevaporization of fluid captured in chamber 240. In FIG. 12A, thereciprocating inner sleeve 175 is shown in a medial position advancingdistally wherein plasma at the resecting electrode edge 180 is resectinga tissue strip 225 that is disposed within lumen 160 of the inner sleeve175. In FIG. 12A-12C, it can be seen that the system operates in firstand second electrosurgical modes corresponding to the reciprocation andaxial range of motion of inner sleeve 175 relative to thetissue-receiving window 176. As used herein, the term “electrosurgicalmode” refers to which electrode of the two opposing polarity electrodesfunctions as an “active electrode” and which electrode functions as a“return electrode”. The terms “active electrode” and “return electrode”are used in accordance with convention in the art—wherein an activeelectrode has a smaller surface area than the return electrode whichthus focuses RF energy density about such an active electrode. In theworking end 145 of FIGS. 10A-11C, the resecting electrode element 195and its electrode edge 180 must comprise the active electrode to focusenergy about the electrode to generate the plasma for tissue resection.Such a high-intensity, energetic plasma at the electrode edge 180 isneeded throughout stroke X indicated in FIG. 12A-12B to resect tissue.The first mode occurs over an axial length of travel of inner sleeve 175as it crosses the tissue-receiving window 176, at which time the entireexterior surface of outer sleeve 170 comprises the return electrodeindicated at 185. The electrical fields EF of the first RF mode areindicated generally in FIG. 12A.

FIG. 12B illustrates the moment in time at which the distal advancementor extension of inner sleeve 175 entirely crosses the tissue-receivingwindow 176 (FIG. 12A). At this time, the electrode sleeve 195 and itselectrode edge 180 are confined within the mostly insulated-wall chamber240 defined by the outer sleeve 170 and distal tip 232. At this moment,the system is configured to switch to the second RF mode in which theelectric fields EF switch from those described previously in the firstRF mode. As can be seen in FIG. 12B, in this second mode, the limitedinterior surface area 250 (FIG. 12C) of distal tip 232 that interfaceschamber 240 functions as an active electrode and the distal end portionof inner sleeve 175 exposed to chamber 240 acts as a return electrode.In this mode, very high energy densities occur about surface 250 andsuch a contained electric field EF can explosively and instantlyvaporize the fluid 244 captured in chamber 240. The expansion of watervapor can be dramatic and can thus apply tremendous mechanical forcesand fluid pressure on the tissue strip 225 to move the tissue strip inthe proximal direction in the tissue extraction lumen 160. FIG. 12Cillustrates such explosive or expansive vaporization of the distentionfluid 244 captured in chamber 240 and further shows the tissue strip 225being expelled in the proximal direction the lumen 160 of inner sleeve175.

FIG. 14 shows the relative surface areas of the active and returnelectrodes at the extended range of motion of the inner sleeve 175,again illustrating that the surface area of the non-insulated distal endsurface 250 is small compared to surface 255 of electrode sleeve whichcomprises the return electrode.

Still referring to FIGS. 12A-12C, it has been found that a single powersetting on the RF source 150 and controller 155 can be configured both(i) to create plasma at the electrode edge 180 of electrode sleeve 195to resect tissue in the first mode, and (ii) to explosively vaporize thecaptured distention fluid 244 in the second mode. Further, it has beenfound that the system can function with RF mode-switching automaticallyat suitable reciprocation rates ranging from 0.5 cycles per second to 8or 10 cycles per second. In bench testing, it has been found that thetissue resecting device described above can resect and extract tissue atthe rate of from 4 grams/min to 8 grams/min without any potential fortissue strips 225 clogging the tissue-extraction lumen 160. In theseembodiments, the negative pressure source 125 also is coupled to thetissue-extraction lumen 160 to assist in applying forces for tissueextraction.

Of particular interest, the fluid-capture chamber 240 defined by sleeve170 and distal tip 232 can be designed to have a selected volume,exposed electrode surface area, length and geometry to optimize theapplication of expelling forces to resected tissue strips 225. In oneembodiment, the diameter of the chamber is 3.175 mm and the length is5.0 mm which taking into account the projecting element 230, provided acaptured fluid volume of approximately 0.040 mL. In other variations,the captured fluid volume can range from 0.004 mL to 0.080 mL.

In one example, a chamber 240 with a captured liquid volume of 0.040 mLtogether with 100% conversion efficiency in and instantaneousvaporization would require 103 Joules to heat the liquid from roomtemperature to water vapor. In operation, since a Joule is a W*s, andthe system reciprocate at 3 Hz, the power required would be on the orderof 311 W for full, instantaneous conversion to water vapor. Acorresponding theoretical expansion of 1700× would occur in the phasetransition, which would results in up to 25,000 psi instantaneously(14.7 psi×1700), although due to losses in efficiency andnon-instantaneous expansion, the actual pressures would be much less. Inany event, the pressures are substantial and can apply significantexpelling forces to the captured tissue strips 225.

Referring to FIG. 12A, the interior chamber 240 can have an axial lengthfrom about 0.5 mm to 10 mm to capture a liquid volume ranging from about0.004 mL 0.01 mL. It can be understood in FIG. 12A, that the interiorwall of chamber 240 has an insulator layer 200 which thus limits theelectrode surface area 250 exposed to chamber 240. In one embodiment,the distal tip 232 is stainless steel and is welded to outer sleeve 170.The post element 248 is welded to tip 232 or machined as a featurethereof. The projecting element 230 in this embodiment is anon-conductive ceramic.

FIG. 13 shows the cross-section of the ceramic projecting element 230which may be fluted, and which in one embodiment has three fluteelements 260 and three corresponding axial grooves 262 in its surface.Any number of flutes, channels or the like is possible, for example fromtwo to about 20. The fluted design increases the availablecross-sectional area at the proximal end of the projecting element 230to push the tissue strip 225, while at the same time the three grooves262 permit the proximally-directed jetting of water vapor to impact thetissue exposed to the grooves 262. In one embodiment, the axial length D(FIG. 12A) of the projecting element 230 is configured to push tissueentirely out of the reduced cross-sectional region 190B of the electrodesleeve element 195. In another embodiment, the volume of the chamber 240is configured to capture liquid that when explosively vaporized provideda gas (water vapor) volume sufficient to expand into and occupy at leastthe volume defined by a 10% of the total length of extraction channel160 in the device, usually at least 20% of the extraction channel 160,often at least 40% of the extraction channel 160, sometimes at least 60%of the extraction channel 160, other times at least 80% of theextraction channel 160, and sometimes at least 100% of the extractionchannel 160.

As can be understood from FIGS. 12A to 12C, the distending fluid 244 inthe working space replenishes the captured fluid in chamber 240 as theinner sleeve 175 moves in the proximal direction or towards itsnon-extended position. Thus, when the inner sleeve 175 again moves inthe distal direction to resect tissue, the interior chamber 240 isfilled with fluid 244 which is then again contained and is thenavailable for explosive vaporization as described above when the innersleeve 175 closes the tissue-receiving window 176. In anotherembodiment, a one-way valve can be provided in the distal tip 232 todraw fluid directly into interior chamber 240 without the need for fluidto migrate through window 176.

In another embodiment, the RF source 150 and controller 155 can beprogrammed to modulate energy delivery parameters during stroke X andstroke Y in FIGS. 12A-12C to provide the optimal energy (i) for plasmaresection with electrode edge 180, and (ii) for explosively vaporizingthe captured fluid in chamber 240.

It should be appreciated that while an RF source is suitable for causingexplosive vaporization of the captured fluid volume, any other energysource can be used and falls within the scope of the invention, such asan ultrasound transducer, HIFU, a laser or light energy source, amicrowave or a resistive heat source.

FIG. 15 is a side view of a fibroid removal system similar to that ofFIG. 1 that includes an endoscope 300 configured for use in hysteroscopyand an RF tissue resecting device 305 configured for introductionthrough the working channel in the endoscope 300.

In FIG. 15, it can be seen that the resecting device has inner and outersleeves 170 and 175 with the inner sleeve 175 reciprocated axiallyrelative to window 176 by a motor 306 in handle 308. The tissueextraction channel 160 in the inner sleeve 175 extends through thehandle 308 in communication with a quick-connect fitting 310. A negativepressure source coupled to a flexible extraction tubing (not shown) canbe connected to fitting 310 to thereby carry resected tissue and fluidto a collection reservoir (cf. FIG. 1). The motor 306 is coupled to anelectrical cable 311 that extends to an electrical source 312 andcontroller 315.

In FIGS. 15 and 16, it can be seen that the endoscope 300 is similar tothe endoscope of FIGS. 1 and 3, except that endoscope 300 in FIGS. 15-16differs in that (i) the endoscope has a different configuration ofworking channel 320 which is curved to provide a pre-determinedresistance to sliding a resecting tool shaft in the channel, and (ii)the endoscope has a different type of disposable adapter component 322that carries a quick-connect fitting 324 for purposes described below.

More in particular, FIGS. 15-16 show that endoscope 300 has a handle ormain body 325 of a metal that is coupled to an extension or shaftportion 328. The elongated shaft 328 can have a diameter ranging from 5mm to 10 mm and in one embodiment is 6.2 mm. The endoscope shaft 328 hasan axial length of 15 to 35 cm and the endoscope 300 can be a 0° scope,or 15° to 30° scope.

The endoscope shaft 328 has an optics channel 106 and first and secondfluid flow channels 108 a and 108 b as shown in the endoscope of FIG. 3.The flow channels 108 a and 108 b (FIG. 3) communicate with Luerconnectors 332 a and 332 b (see FIGS. 15-16). A fluid inflow source 120(FIG. 2) is coupled to first connector 332 a and channel 108 a. Apressure sensor 335 is coupled to second connector 332 b and channel 108b. The pressure sensor 335 is adapted to measure actual intracavitypressure (as described further below) and to send pressure signalscontinuously to controller 315.

The main body 325 of the endoscope 300 includes the angled extensionportion 336 with optics and prism 337 which provides light path LP tothereby allow viewing through optics channel 106. A videoscopic cameracan be coupled to the proximal end 338 of the angled extension portion336. A light source is coupled to light connector 342 on the main body325 of the endoscope.

In FIGS. 15-16, it can be see that the endoscope 300 includes adetachable and disposable adapter component 322 that carries first andsecond seals 346 and 348 that are configured to seal the working channel320 when there is a resecting tool shaft in the channel or in theabsence of a shaft in the channel 320. The more distal seal 348 cancomprise a duck-bill seal or its equivalent that seals the channel whenthere is no tool shaft in channel 320. The more proximal seal 346comprises an elastomeric seal with port 350 that can stretch and impingeon a tool shaft disposed in the channel 322. In one variation shown inFIG. 16, the disposable component 322 can molded of plastic and can bedetachably coupled to main body 325 of the endoscope by a Mock 352. Ano-ring 354 can be provided in an interface between the main body 325 andthe disposable component 322. Any suitable fitting can be used to couplethe disposable component 322 to the main body 325 such as threads,J-locks, etc. FIG. 16 further shows that the disposable adaptercomponent 322 has an interior chamber 353 that has a substantial fluidvolume which can optionally be configured with a manual or automatedpressure relief valve as will be further described below in relatedembodiments.

Referring again to FIGS. 15 and 16, it has been found that the curvedportion 355A of the working channel 322 functions to provide resistanceto unwanted axial sliding of a resecting tool shaft when in use, whileat the same time not providing any resistance to rotation of theresecting device shaft. In use, the electrosurgical resecting device 305as generally shown in FIGS. 1, 4, 10A-14 and 15 is manipulated to resecttissue only by pressing the working end window 176 into a targetedtissue site together with slight rotation of the working end whileresecting tissue. During use, the working end of the RF resecting deviceof FIG. 15 should not be moved axially back and forth to resect tissuechannel as is typical with commercially available RF resecting loopsknown in the prior art. For this reason, the configuration of curvedworking channel 355A shown in FIGS. 15-16 provides a desired increase inresistance to axial sliding of the resecting device shaft in theendoscope which assists in preventing physicians from using thecombination of the present invention (RF resecting device and endoscope)in the manner commonly associated with prior art RF resecting loops. Theshaft of the RF resecting device 305 is also configured to be suitablyflexible to cooperate with the curved working channel. It has been foundthat a curved working channel as described herein does not interferewith the physician's rotation of the resecting device shaft in theworking channel 322, which also is advantageous.

In FIGS. 15 and 16, an embodiment of endoscope 300 has a working channel322 that has a curved or non-straight portion 355A with curved axis 356Athat extends through main body 325 and a straight channel portion 355Bwith straight axis 356B that extends longitudinally through the shaftportion 328 of the endoscope. The curved channel portion 355A can extendover a length AA ranging from about 4 cm to 8 cm and in one embodimentis about 5 cm. The curved channel portion 355A can have a radius Rranging from about 150 mm to 900 mm. In one embodiment, the central axis356A of the curved channel portion 355A at the proximal face 360 of mainbody 325 is offset by a distance having dimension DD which can be about2 mm to 5 mm (see FIG. 16) from the hypothetical central axis 355B ofthe straight channel portion 355B if extended to the proximal face 360of main body 325. In one embodiment, the offset dimension DD is 2.0 mm.In an embodiment, the surface of a least the curved channel portion 355Ain the metal main body 325 can have a coating of titanium nitride orgold which can protect the channel from damage over the working life ofthe endoscope.

In another embodiment (not shown), the working channel 322 in anendoscope 300 similar to that of FIG. 15 can be straight or curved andan alternative mechanism can be used to provide resistance to axialsliding of a tool shaft. In one variation, a compression assembly knownin the art can be used to squeeze an interference element against thetool shaft in the working channel, such as radial inward compression ofan O-ring. FIG. 15 illustrates another mechanism that may be used toindicate or resist axial sliding of a tool shaft in the working channel.As can be seen in FIG. 15, the RF resecting device has a stiffenersleeve 370 disposed around the proximal end 372 of outer sleeve 170. Thestiffener sleeve 370 can have a length of 4 to 6 cm and is configuredwith 5 to 50 annular grooves or detents 375 that cooperate with a springelement (not shown) in the adapter component 322 for engaging thedetents 375 to provide tactile feedback to the physician relating toaxial sliding of the tool shaft.

In general, the endoscope 300 comprises a main body 325 and extendedshaft portion 328 that extends longitudinally to a distal end, a firstchannel extending from the handle end to the distal end coupleable to afluid inflow source, a second channel extending from the handle end tothe distal end configured for fluid outflows and/or receiving an RFresecting device, wherein the second channel has first straight portionand a second curved portion, and a disposable component carrying atleast one seal detachably coupled to the endoscope main body and thesecond channel. In one variation, the device has first and second sealselements carried in the disposable component configured to seal thesecond channel with or without a tool shaft disposed therein. In onevariation, a third channel is configured for coupling to a pressuresensor 335 (see FIGS. 15-16). A fourth channel is configured as anoptics channel for viewing the uterine cavity A fifth channel isconfigured as a light guide extending from the main body of theendoscope to the distal end of the extended shaft portion 328. Theendoscope can have a pressure sensor 335 that is configured to sendpressure signals to a controller 315 to control fluid inflows and fluidoutflows through the endoscope to thereby control fluid pressure in theuterine cavity. The controller can be operatively coupled to the fluidinflow and outflow sources to contemporaneously (i) control pressurewithin the uterine cavity by modulating the positive and negativepressure sources and (ii) control operating parameters of theelectrosurgical resecting device. The controller 315 can be adapted toselectively control flows to the uterine cavity through a flow channelat any rate between 0 ml/min and 750 ml/min. In another aspect of theinvention, the controller 315 can be adapted to selectively controlpressure in the uterine cavity at any level between 0 mmHg and 150 mmHg.The controller 315 can be adapted to selectively control outflows fromthe uterine cavity through a channel in the system at any rate between 0ml/min and 750 ml/min. In one variation, the pressure sensor 335 (FIG.15) is disposable and is detachably coupled to a proximal end of achannel that has a cross-sectional area of greater than 0.1 mm², greaterthan 0.5 mm² or greater than 1.0 mm².

FIGS. 17 and 18 illustrate another variation of endoscope 500 that isconfigured for use in hysteroscopy that includes mechanisms and systemsfor controlling pressure in a uterine cavity during a fibroid removalprocedure. In one variation, the endoscope 500 and system is adapted toautomatically reduce intracavity pressure within a predetermined timeinterval after a set point of intracavity pressure has been reached. Thepredetermined set point can be 50 mm Hg, 60 mm Hg, 70 mm Hg, 80 mm Hg,90 mm Hg, 100 mm Hg, 110 mm Hg, 120 mm Hg, 130 mm Hg, 140 mm Hg, 150 mmHg, 160 mm Hg, 170 mm Hg or 180 mm Hg. In one variation, thepredetermined pressure is 150 mm Hg. The predetermined interval can bein a range between 1 second and 10 seconds and in one variation is 5seconds. In another variation, the system includes a pressure reliefvalve for releasing pressure at a predetermined maximum pressure whichcan in the range of 150 mm Hg to 200 mm Hg and in one variation is 200mm Hg. Of particular interest, the system is adapted to respond to ameasurement of “actual” intracavity pressure measured by a pressuresensor in direct fluidic communication with the uterine cavity. In priorthe art, fluid management systems that are adapted to releaseintracavity pressure at a predetermined set point use only an“estimated” intracavity pressure that is estimated by a softwarealgorithm based on signals relating to fluid inflows communicated to aflow controller. Such prior art systems and algorithms are not capableof accurately measuring “actual” intracavity pressure.

In FIGS. 17-18, it can be seen that endoscope 500 has standard featuresincluding a viewing channel 508, a light channel comprising optic fibersin shaft portion 512, a working channel 510 and one or more fluid inflowor outflow channels. The shaft portion 512 of the endoscope extendsabout central longitudinal axis 515. The endoscope body is reusable andsterilizable as in known in the art. A handle or main body portion 516of the endoscope body couples to the shaft 512 and carries an eyepiece517 and luer connectors (not shown) communicating with first and secondchannels for fluid inflows and outflows as described previously. A lightconnector is indicated at 518.

As further can be seen in FIG. 17, a proximal endoscope or adaptercomponent 520 comprises a disposable adapter body which is attachable tothe proximal end of the endoscope main body. The adapter component 520can attached by either threads, Mock or a snap fitting at interface 522in a configuration that rotationally aligns the channel or lumen portionin component 520 with the channel in the endoscope main body 505.

In one aspect of the invention, the proximal end 524 of the adaptercomponent 520 is configured as a mating portion of a quick-connectfitting 525. The quick-connect fitting 525 and O-ring 528 can be used tocouple an outflow tubing 530 directly to the proximal end of theendoscope assembly 500 to allow the system to be used in a diagnosticmode. A diagnostic mode consists of the physician performing adiagnostic procedure before using a resecting probe. Thus, when aresecting probe is not inserted through the endoscope the physician canconnect the saline return flow tubing directly to the quick-connectfitting 525 and circulates distention fluid through an inflow channel inthe endoscope device and outward through the working channel and outflowtubing coupled to the quick-connect 525 to distend the uterine cavity tothereby allow viewing of the cavity.

The adapter component 520 further carries seals 530 a and 530 b whichcomprise seals for (i) preventing fluid outflows through the workingchannel and adapter when there is no resecting tool disposed theendoscope and for (ii) providing a seal around a resection tool shaftwhen such a tool is disposed in the endoscope. These seals 530 a and 530b can be integrated into a one component or be spaced apart as shown inone variation in FIG. 17.

In one aspect of the invention, as described above, the endoscopeassembly includes a valve system configured to automatically reduceuterine cavity pressure within a predetermined time interval after a setpoint of intracavity pressure has been reached. In one variation, asstated above, the predetermined pressure is 150 mm Hg and thepredetermined interval is 5 seconds. In one variation, a solenoid reliefvalve 540 is operatively coupled to a controller 545 and is adapted torelease at least a predetermined volume of distention fluid from thesystem (endoscope assembly) within a predetermined time interval toinsure a very rapid release of pressure in the uterine cavity. In onevariation, the predetermined volume is at least 0.1 cc, 0.5 cc, 1 cc, 2cc, 3 cc, 5 cc or 10 cc within 1 second to release intracavity pressure.The controller 545 receives pressure signals from a pressure sensorcoupled directly to an outflow channel in the endoscope as describedpreviously. The controller 545 also can be configured to close therelief valve 540 after a predetermined time interval during whichintracavity pressure is below the set point, which interval can be atleast 1 second, 2 seconds, 5 seconds or 10 seconds.

In one variation shown schematically in FIG. 17, the adapter component520 is configured to carry the solenoid or relief valve 540 which iscoupled to a system controller 545 through cable 546. The solenoidrelief valve 540 also can include an integrated pressure sensor 548Acoupled to the system controller 545 through cable 546 wherein apressure signal at the predetermined pressure will then actuate thesolenoid valve 540 to release fluid from the interior channel to theenvironment to lower intracavity pressure. The pressure sensor 548Acommunicates with the uterine cavity through fluid in the workingchannel 510 (around a tool in channel 510) to directly sense pressure inthe uterine cavity.

In another variation shown in FIG. 19, an independent pressure sensor548B is shown that communicates with an independent flow channel 552 inthe endoscope shaft 512 to allow direct measurement of uterine cavitypressure. The pressure sensor 548B again is operatively connected tocontroller 545.

In another variation, a signal of a selected level of high pressure froma pressure sensor can terminate RF energy delivery orreciprocation/rotation of a resecting device. In another variation, asignal of a selected level of high pressure from a pressure sensor cantrigger a change in inflows or outflows caused by a pump component ofthe fluid management system.

In FIGS. 17 and 18, if can be seen that the interior of the adapter 520and interior of endoscope main body portion 516 are configured with amating open space or expanded offset-axis channel portion 550 thatenables optimal functioning of the solenoid relief valve 540. As can beseen in FIG. 19, a probe or tool shaft 555 of a resecting device isshown after having been introduced through the endoscope 500 and theshaft 555 has a dimension that occupies a substantial cross-section ofthe tool-receiving working channel 510. In the variation of FIGS. 17 and19, the tool shaft 550 is introduced, in order, (i) through proximal end524 of the adapter 520 and through channel 560 having longitudinal axis565 in the proximal portion of the adaptor that has length AA, (ii)through interior expanded offset-axis channel portion 550 in the adapter520 and proximal portion of handle 516 that has diameter D2, and (iii)through distal channel 510 (diameter D3) of the endoscope shaft portion512. As can be seen in FIGS. 17-18, the diameter D1 of channel 560 isdimensioned to accommodate a stiffener sleeve 564 that extends around aproximal portion of probe shaft 555 adjacent the handle 566 of theresecting probe 100 (see FIG. 1). Referring to FIG. 17, it can be seenthat channel 560 extends along axis 515 and the offset-axis channelportion 550 extends along a central axes 570 a, 570 b and 570 c, and thedistal channel 510 extends along axis 575.

FIG. 19 depicts tool shaft 555 disposed within the endoscope assemblyand it can be seen that the volume of the offset-axis channel portion550 enables optimal functioning of the solenoid relief valve 540 sincethe valve interfaces with a substantial volume of a fluid column thatextends to the uterine cavity. As can be seen schematically in FIGS. 20Aand 20, the relief valve 540 interfaces with a large volume of fluid 576in expanded offset-axis channel 550 which communicates with the uterinecavity through a smaller volume of fluid in the annular space 577 aroundshaft 555 in elongated distal channel 510 that extends through theassembly. As can be easily understood, the release of fluid from channelportion 550 responds to the pressure differential between interiorchannel portion 550 and the external environment, which upon opening therelief valve 540, can result in very rapid release of fluid as describedabove. In one variation, the volume of expanded offset-axis channel 550is at least 1 cc, 5 cc or 10 and the fluid release rate can be at least0.1 cc, 0.5 cc, 1 cc, 2 cc, 3 cc, 5 cc or 10 cc within 1 second torelease pressure in the uterine cavity. Thereafter, the pressuredifferential between the channel portion 550 and the uterine cavity willresult an instantaneous reduction in pressure in the uterine cavity.

In another aspect of the invention, referring to FIGS. 20A-20B, thefluid volume 576 in the expanded offset-axis channel 550 is needed toprevent transient pressure spikes on pressure sensor 548A which can beintroduced by axial movement of probe shaft 555 in the assembly. It canbe easily understood that if the tool shaft 555 is moved axially in thevariation of FIG. 20B, there could be transient effects on any pressuresensor having fluid contact with the small annular space 577.

In another aspect of the invention, the small annular space 577 can betransiently impinged on by flexing the assembly during use or by mucous,blood, and/or tissue debris clogging the annular space 577. Thus, thefluid volume 576 in the expanded offset-axis channel 550 thus provides,in effect, a fluid reservoir in which mucous, tissue debris, etc. cansettle or circulate and reduce the chance of debris impinging on theflow path through the relief valve 540. If a pressure sensor ispositioned in channel 550, the fluid volume 576 in offset-axis channel550 further functions as a buffering reservoir against transient changesin the cross-section of annular space 577 due to flexing of the device.It can be understood from FIG. 20B that a sensor 540′ in an annularspace 577′ (without a buffering reservoir volume 576 of FIG. 20A) canlead to a clogged sensor interface or fluctuations in pressure signalswhich would detract from system operation.

Referring to FIG. 21, another embodiment has an optical sensor 580 inexpanded offset-axis channel 550 that cooperates with a marking 585 onthe probe shaft 555 to determine the axial location of the shaft 555relative to the sensor. In one variation, the position sensing system isoperatively coupled to controller 545 to terminate RF delivery to theprobe in the event the physician withdrew the probe working end into theworking channel 510 with RF energy still activated. Contacting theplasma resecting edge with the endoscope could damage the endoscope.

In another variation, referring to FIG. 22, a passive pressure reliefvalve 590 can be disposed in the component 520 to release pressure at apredetermined pressure, for example, at least 150 mm Hg, 160 mm Hg, 170mm Hg, 180 mm Hg, 190 mm Hg or 200 mm Hg. This passive relief valve canbe used in combination with the controller operated solenoid.

In another variation, a temperature sensor can be disposed in thecomponent 520 to measure temperature of the fluid in channel 550 as anadditional safety mechanism. It should be appreciated that a pressuresensor can be provided in any embodiment of FIGS. 17-22 in communicationwith the expanded off-axis chamber 550, in the location of the pressurerelief valve shown in FIGS. 17-22.

Although particular embodiments of the present invention have beendescribed above in detail, it will be understood that this descriptionis merely for purposes of illustration and the above description of theinvention is not exhaustive. Specific features of the invention areshown in some drawings and not in others, and this is for convenienceonly and any feature may be combined with another in accordance with theinvention. A number of variations and alternatives will be apparent toone having ordinary skills in the art. Such alternatives and variationsare intended to be included within the scope of the claims. Particularfeatures that are presented in dependent claims can be combined and fallwithin the scope of the invention. The invention also encompassesembodiments as if dependent claims were alternatively written in amultiple dependent claim format with reference to other independentclaims.

What is claimed is:
 1. An endoscopic system, comprising: an endoscopehaving a main body and a shaft portion extending distally therefrom,wherein the endoscope includes a working channel extending through themain body and the shaft portion; wherein the working channel includes aproximal portion and a distal portion intersecting within the main body;wherein the distal portion extends linearly along a distal axis to adistal end of the shaft portion; wherein a proximal opening of theproximal portion is disposed in a proximal face at a proximal end of theendoscope; wherein the distal axis extended proximally intersects theproximal face and is laterally offset from the proximal opening at theproximal face; and a tissue resecting probe including an outer sleeveand an inner sleeve configured to move within and relative to the outersleeve, the tissue resecting probe being configured for introductionthrough the working channel.
 2. The endoscopic system of claim 1,wherein the working channel is configured to resist axial movement ofthe tissue resecting probe within the working channel while permittingrotational movement of the tissue resecting probe within the workingchannel.
 3. The endoscopic system of claim 1, wherein the shaft portionincludes an optics channel in communication with an angled extensionportion of the main body.
 4. The endoscopic system of claim 1, whereinthe shaft portion includes a first fluid channel configured to becoupled to a fluid source and a second fluid channel configured to becoupled to a pressure sensor.
 5. The endoscopic system of claim 1,further comprising: a quick-disconnect adapter component detachablycoupled to a proximal end of the main body.
 6. The endoscopic system ofclaim 1, wherein a centerline of the proximal portion of the workingchannel is non-coaxial with the distal axis.
 7. The endoscopic system ofclaim 6, wherein the centerline of the proximal portion of the workingchannel is a curved centerline.
 8. The endoscopic system of claim 6,wherein the curved centerline has a radius ranging from 150 mm to 900mm.
 9. The endoscopic system of claim 1, wherein the proximal portion ofthe working channel is non-parallel with the distal portion of theworking channel.
 10. The endoscopic system of claim 1, wherein theproximal opening of the proximal portion is laterally offset from thedistal axis by 2 mm to 5 mm.
 11. The endoscopic system of claim 1,wherein the proximal opening of the proximal portion is laterally offsetfrom the distal axis by more than 2 mm.
 12. The endoscopic system ofclaim 11, wherein the proximal opening of the proximal portion islaterally offset from the distal axis by less than 5 mm.
 13. Anendoscopic system, comprising: an endoscope having a metallic main bodyand a metallic shaft portion extending distally therefrom, wherein theendoscope includes a working channel extending through the main body andthe shaft portion; wherein the working channel includes a proximalportion and a distal portion extending distally from the proximalportion, the distal portion extending distally from the main body alonga straight distal centerline to a distal end of the shaft portion andthe proximal portion extending proximally within the main body along aproximal centerline to a proximal opening in a proximal face of theendoscope at a proximal end of the endoscope, the proximal centerlineextending non-parallel to the distal centerline; wherein the distalcenterline extended proximally from the distal portion through theproximal face is laterally offset from the proximal opening at theproximal face.
 14. The endoscope of claim 13, wherein the proximalcenterline is a curved centerline.
 15. The endoscope of claim 13,wherein the proximal centerline extends through a center of the proximalopening.
 16. An endoscopic system, comprising: an endoscope having ametallic main body and a shaft portion extending distally therefrom,wherein the endoscope includes a working channel extending through themain body and the shaft portion; a tissue resecting probe including anouter sleeve and an inner sleeve configured to move within and relativeto the outer sleeve, the tissue resecting probe being disposed withinthe working channel; wherein the working channel includes a distalportion extending distally from the main body along a straight distalcenterline to a distal end of the shaft portion and a proximal portionextending proximally within the main body to a proximal opening in aproximal face of the main body at a proximal end of the endoscope;wherein the distal centerline extended proximally from the distalportion through the proximal face is laterally offset from the proximalopening at the proximal face; wherein the outer sleeve is free to rotaterelative to the endoscope.
 17. The endoscopic system of claim 16,wherein a centerline of the proximal portion intersects the distalcenterline within the main body.
 18. The endoscopic system of claim 16,wherein the working channel resists axial movement of the tissueresecting probe therein.
 19. The endoscopic system of claim 16,including a quick disconnect port and valve structure removably disposedat a proximal end of the main body in fluid communication with theproximal opening.